Apparatus and methods for optical stimulation of neural tissues

ABSTRACT

An apparatus for stimulating a neural tissue of a living subject. The neural tissue is characterized with a thermal diffusion time, T d . The apparatus includes an energy source for generating optical energy and delivering means coupled to the energy source for delivering the generated optical energy to a target neural tissue. The delivering means is configured to in operation deliver the generated optical energy with a radiant exposure that causes a thermal gradient in the target neural tissue, thereby stimulating the target neural tissue, and to deliver the optical energy in pulses with a pulse duration T p  such that T p &lt;T d .

CROSS-REFERENCE TO RELATED PATENT APPLICATION

This application is a divisional application of and claims the benefitof U.S. patent application Ser. No. 11/945,649, filed Nov. 27, 2007,entitled “APPARATUS AND METHODS FOR OPTICAL STIMULATION OF NEURALTISSUES,” which is allowed and claims the benefit, pursuant to 35 U.S.C.§119(e), of U.S. provisional patent application Ser. No. 60/861,673,filed Nov. 27, 2006, entitled “APPARATUS AND METHODS FOR OPTICALSTIMULATION OF NEURAL TISSUES,” by Anita Mahadevan-Jansen, Jonathon D.Wells and E. Duco Jansen. The disclosure of the above applications areincorporated herein by reference in its entirety.

STATEMENT AS TO RIGHTS UNDER FEDERALLY-SPONSORED RESEARCH

This invention was made with government support under Contract No.FA9550-04-1-0045 awarded by the United States Department of Defense andContract No. RO1 NS052407-01 awarded by the National Institute ofHealth. The government has certain rights in the invention.

Some references, which may include patents, patent applications andvarious publications, are cited in a reference list and discussed in thedescription of this invention. The citation and/or discussion of suchreferences is provided merely to clarify the description of the presentinvention and is not an admission that any such reference is “prior art”to the invention described herein. All references cited and discussed inthis specification are incorporated herein by reference in theirentireties and to the same extent as if each reference was individuallyincorporated by reference. In terms of notation, hereinafter, “[2]”represents the nth reference cited in the reference list. For example,[2] represents the 2nd reference cited in the reference list, namely,Wells, J. D., Kao, C., Jansen, E. D., Konrad, P., Mahadevan-Jansen, A.,Application of Infrared Light for in vivo Neural Stimulation. Journal ofBiomedical Optics, 2005. 10: p. 064003.

FIELD OF THE INVENTION

The present invention relates generally to the stimulation of neuraltissues, and more particularly to apparatus and methods for facilitationand/or enhancement of optical stimulation of neural tissues in vivo,with the use of at least one of one or more chromophores and one or moreoptical agents.

BACKGROUND OF THE INVENTION

For over a century, the traditional method of stimulating neuralactivity in humans during medical procedures has been based onelectrical methods, which has undergone few modifications over the yearsand remains the gold standards to date. Electrical stimulation isutilized to identify the connectivity and functionality of specificnerve roots to be selectively avoided or resected as well as to create aunique map of functional structures that varies among individuals duringbrain tumor resection. However, electrical stimulation is prone toelectrical interference from the environment, high frequency artifactsassociated with the electrical signal used, intrinsic damage caused bythe electrodes used for stimulation themselves, population response dueto the recruitment of multiple axons, which prevents simultaneousstimulation and recording of adjacent areas, and in general poor spatialspecificity.

Alternative approaches exist for stimulation of neural fibers (tissues)by optical irradiation. Researches on the excitability of neural tissueas a by-product of laser therapies and the capability of light inmodulating its electrical conductivity have been reported [1,2].

The use of lasers in medical procedures can be grouped into two distinctcategories, therapeutic and diagnostic or imaging applications. Intherapeutic procedures, the interaction between the laser and biologicaltissue results in a light distribution and absorption and subsequentphotobiological effect that can be classified into, at least, threemechanistic categories, (1) photochemical, (2) photothermal, and (3)photomechanical [3]. Action potential propagation in neurons throughchemical, thermal, and mechanical means [4-6] have been demonstrated.Photochemical effects depend on the absorption of light to act as areagent in a stoichiometric reaction catalyzed by some photosensitizer.An example of a photochemical effect is the production of reactivechemicals (ultimately leading to oxygen radicals) reported inphotodynamic therapy (PDT) by the combination of an injected extrinsicdye, singlet oxygen, and light [7-9]. Frequently, biostimulation is alsoattributed to photochemical interactions thought to target naturalintrinsic agents, although this is not scientifically ascertained[10,11]. Photothermal effects result from the transformation of absorbedlight energy to heat, which may lead to hyperthermia, coagulation, orablation of the target tissue [12]. Photomechanical effects aresecondary to rapid heating with short laser pulses (<1 μs) that producemechanical forces, such as explosive events and laser-induced pressurewaves able to disturb cells and tissue [13, 14]. This classification oflaser tissue interactions can be further separated into three distinctcategories including; thermoelastic expansion, ablative recoil, andexpansion secondary to phase change [15].

In the majority of therapeutic laser applications, the laser-tissueinteraction is mediated by a thermal or thermo-mechanical processdepending on the operational parameters of the laser, such as wavelength(λ), pulse duration (τ), and laser radiant exposure or irradiance. Ingeneral, the objective is to damage tissue locally by exploiting highspatial precision and the ability to couple laser light into fiberoptics for minimally invasive delivery to the tissue [16]. While opticalnerve stimulation does exploit these distinctive delivery advantages,the therapeutic result for this technique is a stimulation effect intissue rather than destruction. Laser radiant exposure (J/cm²)associated with these procedures results in either reversible ornon-reversible thermal or mechanical alterations of the tissue. The keyparameter, wavelength, determines light distribution in the tissuedictated by wavelength dependent optical properties. The energy densityand subsequent temperature rise resulting from absorption of opticalenergy is inversely proportional to the penetration depth and dependingon the laser radiant exposure, a temperature increase is induced in thetissue (for comprehensive review see: [17]). While photochemicalprocesses are often governed by a specific reaction pathway,photothermal effects are non-specific and are mediated by absorption ofoptical energy and secondly governed by fundamental principles of heattransport. Subsequent effects in the target tissue are determined by thetemperature rise and the duration of the temperature exposure asdescribed by an Arrhenius rate process [18].

It is important to point out that the duration of the laser exposure,which is largely similar to the interaction time itself, distinguishesand primarily controls these photobiological processes. According to agraph of the laser radiant exposure versus the duration of pulse widththe time scale can roughly be divided in three major sections [3];continuous wave or exposure times>1 s for photochemical interactions,100 s down to 1 μs for photothermal interactions, and 1 μs and shorterfor photomechanical interactions, as shown in FIG. 10. These boundariesare not strict and adjacent interaction types cannot always beseparated. For example, in the range of 1 μs to several hundreds of μs,the interaction mechanism has photothermal as well as photomechanicalcomponents, while many photochemical interactions also exhibitphotothermal components.

Great clinical relevance would be gained if optimal laser parameters forsafe and effective stimulation of nerves could be determined from thelaser-tissue interactions that occur during optical nerve stimulation inclinical implementations. Understanding the biophysical mechanism willultimately help to refine an optimal laser parameter set to effectivelytarget the diverse morphology of neural tissue types as well as identifypossible clinical applications and limitations for this nervestimulation modality.

Therefore, a heretofore unaddressed need exists in the art to addressthe aforementioned deficiencies and inadequacies.

SUMMARY OF THE INVENTION

The present invention, among other things, discloses methods and systemsfor facilitation and/or enhancement of optical stimulation of neuraltissues, with the use of exogenous chromophores, endogenous chromophoresand/or optical agents. The exogenous agents may be external to theneurons and/or be loaded into the intracellular space, so long as theagents act to enhance the underlying mechanism of optical stimulationthrough a thermally mediated process and/or directly facilitate thisoptical stimulation of neural tissue using a chromophore normally notpresent in tissue to directly cause the thermally mediated mechanism bywhich pulsed laser stimulation occurs. Similarly, endogenouschromophores can be targeted near the cell membrane to cause efficientstimulation without significant absorption (i.e., heat generation) fromsurrounding tissues.

Generally, wavelengths of light for efficiently optical stimulation oftissues are determined by the tissue absorption spectrum, i.e., theintrinsic tissue absorption properties are primarily responsible forefficient stimulation with minimal tissue damage. The mechanism ofaction for this phenomenon is related to establishing a thermal gradientin the tissue at the level of the neuronal cell membrane that causessubsequent stimulation due to the increase in temperature. Furthermore,with the addition of exogenous/endogenous chromophores and/or opticalagents in the target tissue, the absorption can be changed based on thematerial properties of that deposited enhancer. These properties may beoptimized to not only absorb light efficiently (thus establish thethermal gradient in tissue) at the appropriate energy levels, but alsoact as a heat sync to minimize thermal damage in tissue associated withthis nerve stimulation phenomenon. With the thermal mechanism forstimulation of neural tissue, any wavelength of light can be used forstimulation, provided the light is absorbed by the optical enhancingmedium and transferred to heat locally near the cell membrane. Anoptimal wavelength for use of an exogenous/endogenous chromophore and/oroptical agent is one that has minimal absorption in neural tissue, yetoptimal absorption (i.e. absorption that is higher than that of thetissue) in the enhancing material, and one that localizes the thermalgradient near the cell membrane without significant absorption fromother tissue layers.

The method according to the present invention has advantages over theexisting optical neural stimulation methodology by: 1) increasingspatial resolution to only the area where exogenous chromophore isloaded or placed, 2) increasing the number of lasers and wavelengthsavailable for optical stimulation by changing the absorption propertiesof the target tissue (thus allowing stimulation), 3) enhancing existingoptimal wavelengths to decrease the amount of laser energy required forstimulation as well as possibly increasing the energy required fortissue damage by acting as a heat sync in the nerve, 4) allowing thepossibility of non-invasive stimulation by coating/loading the targetneurons prior to stimulation and the use of a laser with a wavelengththat is both capable of penetrating soft tissue as well as being highlyabsorbed by the input chromophore.

In one aspect, the present invention relates to a method of opticallystimulating a neural tissue of a living subject. In one embodiment, themethod includes the steps of generating at least one beam of radiation;introducing at least one of one or more chromophores and one or moreoptical agents to a target neural tissue; and delivering the at leastone beam of radiation to the target neural tissue, wherein the at leastone beam of radiation is delivered with a radiant exposure that causes athermal gradient in the target neural tissue, thereby stimulating thetarget neural tissue.

In one embodiment, the at least one of one or more chromophores and oneor more optical agents are introduced to the intracellular space of thetarget neural tissue. In another embodiment, the at least one of one ormore chromophores and one or more optical agents is introducedexternally to the neurons of the target neural tissue.

The at least one beam of radiation has an intensity between a firstintensity threshold and a second intensity threshold that is greaterthan the first intensity threshold, wherein the first intensitythreshold is a stimulation threshold of the target tissue, and whereinthe second intensity threshold is an ablation threshold of the targettissue. The ratio of the second intensity threshold to the firstintensity threshold is a function of a wavelength of the at least onebeam of radiation. In one embodiment, the ratio of the second intensitythreshold to the first intensity threshold is in a range from 1 to 200,preferably in a range from 4 to 6. The at least one beam of radiation isdelivered to the target neural tissue with the radiant exposure no morethan 5.0 J/cm², preferably no more than 2.0 J/cm².

In one embodiment, the at least one beam of radiation has a wavelengthselected such that when delivered to the target neural tissue, it causesa maximal temperature increase and a minimal tissue damage in the targetneural tissue.

In one embodiment, the target neural tissue is characterized with athermal diffusion time, T_(d), and wherein the at least one beam ofradiation comprises a plurality of pulses with a pulse duration, T_(p),such that T_(p)<T_(d).

In another aspect, the present invention relates to a method ofoptically stimulating a neural tissue of a living subject. In oneembodiment, the method comprises the step of introducing at least one ofone or more chromophores and one or more optical agents to a targetneural tissue; and exposing the target neural tissue to a beam ofradiation with a radiant exposure for an amount of time sufficient toestablish a thermal gradient therein, thereby stimulating the targetneural tissue, wherein the beam of radiation has an intensity between astimulation threshold of the target neural tissue and an ablationthreshold of the target neural tissue that is greater than thestimulation threshold of the target neural tissue.

The beam of radiation has a wavelength selected such that when deliveredto the target neural tissue, it causes a maximal temperature increaseand a minimal tissue damage in the target neural tissue.

The target neural tissue is characterized with a thermal diffusion time,T_(d), and wherein the beam of radiation comprises a plurality of pulseswith a pulse duration, T_(p), such that T_(p)<T_(d).

In yet another aspect, the present invention relates to a method ofoptically stimulating a neural tissue of a living subject. The neuraltissue of interest is characterized with a thermal diffusion time,T_(d). In one embodiment, the method has the step of delivering opticalenergy to a target neural tissues in pulses with a pulse duration T_(p)such that T_(p)<T_(d), and wherein the optical energy is delivered witha radiant exposure that causes a thermal gradient in the target neuraltissue, thereby stimulating the target neural tissue. The method furtherhas the step of introducing at least one of one or more chromophores andone or more optical agents to a target neural tissue prior to thedelivering step. The target neural tissue receives the optical energyfor an amount of time sufficient to initiate action potentialpropagation within the target neural tissue.

In one embodiment, the delivering step includes the step of focusing theoptical energy on the target neural tissue so that the target neuraltissue propagates an electrical impulse.

In a further aspect, the present invention relates to an apparatus forstimulating a neural tissue of a living subject, where the neural tissueis characterized with a thermal diffusion time, T_(d). In oneembodiment, the apparatus has an energy source for generating opticalenergy; and a delivering means coupled to the energy source fordelivering the generated optical energy to the target neural tissue. Thedelivering means is configured to deliver the generated optical energywith a radiant exposure that causes a thermal gradient in the targetneural tissue, thereby stimulating the target neural tissue, and theoptical energy is delivered in pulses with a pulse duration T_(p) suchthat T_(p)<T_(d).

The apparatus further has a controlling means operably coupled to theenergy source and the delivering means and the target neural tissue. Inone embodiment, the controlling means includes a first detector operablycoupled to the energy source for measuring the optical energy generatedfrom the energy source; a second detector operably coupled to the targetneural tissue for measuring the thermal gradient in the target neuraltissue; and a computer operably coupled to the first detector and thesecond detector for evaluating the optical stimulation of the targetneural tissue.

In one embodiment, the delivering means includes a connector having abody portion defining a channel extending from a first end to a secondend; one or more optical fibers housed in the channel for transmittingthe optical energy; and a probe operably coupled to the second end ofthe connector and having an end portion for delivering the opticalenergy to a target neural tissue. The delivering means may furtherinclude a selecting device operably coupled to the connector forselectively delivering the optical energy through at least one of theone or more optical fibers. Additionally, the delivering means may alsoinclude a movable stage that is operably coupled to the probe such thatthe probe is movable with the movable stage three-dimensionally toselectively deliver the optical energy to one or more neural fibers ofthe target neural tissue.

In another embodiment, the delivering means has a first optical meansfor directing the optical energy to a desired direction; and a secondoptical means for focusing the optical energy directed by the firstoptical means to a target neural tissue. The first optical means and thesecond optical means are positioned such that the energy source, thedelivering means and the target neural tissue are positioned along anoptical path. Each of the first optical means and the second opticalmeans comprises at least one of one or more optical mirrors, one or moreoptical lenses, one or more optical couplers, and one or more opticalfibers.

In one embodiment, the energy source has a laser capable of generating abeam of optical energy having a wavelength that is fixed or tunable. Thelaser includes a pulsed infrared laser, such as a free electron laser,an Alexandrite laser, a solid state laser, a CO₂ laser, a tunableoptical parametric oscillator (OPO) laser system, an N₂ laser, anexcimer laser, a Holmium-doped:Yttrium Aluminum Garnet (Ho:YAG) laser,or an Erbium doped: Yttrium Aluminum Garnet (Er:YAG) laser.

These and other aspects of the present invention will become apparentfrom the following description of the preferred embodiment taken inconjunction with the following drawings, although variations andmodifications therein may be affected without departing from the spiritand scope of the novel concepts of the disclosure.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows schematically an experimental setup for nerve surfacetemperature measurements with a IR (thermal) camera according to oneembodiment of the present invention.

FIG. 2 shows an effect of laser pulse duration on stimulation thresholdradiant exposure. Three lasers with comparable tissue absorptioncoefficients were used; the FEL (5 μsec), Ho:YAG (350 μsec), and tunablesolid state Aculight laser (1-5 msec). All lie well outside stressconfinement, but are still thermally confined.

FIG. 3 shows DP-OCT measurements of nerve surface displacement resultingfrom Ho:YAG laser irradiation, (a) a typical recording of the opticalpath length change of the nerve surface relative to a stationarycoverslip from near threshold radiant exposure (0.4 J/cm2) indicatingthermoelastic expansion on the order of 300 nm, and (b) a total of 18measured surface displacements over the normal range of use for opticalstimulation radiant exposures.

FIG. 4 shows CNAP signal onset time for two different pulse durations.Assume the time for conduction is constant after the pulse energydeposition, (a) Schematic illustrating the distance from stimulation andrecording for (b) and (c), (b) CNAP recorded from stimulation at t=0using a 2.5 msec pulse duration with the Aculight optical nervestimulator, and (c) CNAP recorded from stimulation at t=0 using a 8.0msec pulse duration with the Aculight optical nerve stimulator. Theserecording prove that all laser energy is required before the onset ofthe CNAP can occur.

FIG. 5 shows an effect of laser radiant exposure on time of CNAPrecording onset stimulated at t=0 using a 6 msec pulse width with theAculight optical nerve stimulator. (a) schematic illustrating thedistance from stimulation and recording for (b) and (c), and (b) CNAPrecorded from optical stimulation with 0.6 J/cm², and (c) CNAP recordedfrom optical stimulation with 1.2 J/cm². These recording illustrate thata specific tissue temperature change is required for the onset of theCNAP can occur.

FIG. 6 shows a temperature spatial profile measurement of the nervesurface in vivo using the thermal camera from UT Austin immediatelyfollowing optical stimulation. Threshold (0.4 J/cm²) radiant exposurewith a 600 micron fiber yields a peak tissue temperature=35.86° C., peaktemperature rise=8.95° C., and average temperature rise=3.66° C. Thecalculated Gaussian spot=0.37 mm². The position of the maximum pixel for0.4 J/cm² stimulation (stars) and Gaussian fit (solid line) oftemperature profile for maximum linescan in x and y are below.

FIG. 7 shows (a) a maximum temperature in hydrated tissue (diamonds) andpeak temperature rise in tissue (squares) as a function of radiantexposure immediately following laser stimulation, where stimulationthreshold occurs between 0.3-0.4 J/cm², onset of minimal thermal changesin tissue occurs at 43° C., which corresponds to the onset of thermaldamage seen in previously published histological analysis (0.8-1.0J/cm2), and (b) average temperature rise from multiple trials (n=12).

FIG. 8 shows a temperature profile of peripheral nerve in time, laserstimulation near threshold (0.4 J/cm²) (a) and at over 2 times threshold(0.8 J/cm²) (b). The experimental thermal relaxation time of peripheralnerve tissue based on the equation shown in the figure is 90 msec.

FIG. 9 shows a steady-state maximum temperature increase in nerve tissuefrom Ho:YAG laser stimulation, (a) temperature rise from 0.45 J/cm²radiant exposure pulses at 2 Hz stimulation frequency, (b) Temperaturerise from 0.65 J/cm² radiant exposures at 2 Hz stimulation frequency,(c) temperature rise from 0.41 J/cm² threshold radiant exposures at 5 Hzstimulation frequency, and (d) temperature rise from 0.63 J/cm²threshold radiant exposures at 5 Hz stimulation frequency.

FIG. 10 shows confinement zones based on penetration depth and pulselength for soft tissue. Note that that the three lasers used are allthermally confined, but not stress-confined.

DETAILED DESCRIPTION OF THE INVENTION

The present invention is more particularly described in the followingexamples that are intended as illustrative only since numerousmodifications and variations therein will be apparent to those skilledin the art. Various embodiments of the invention are now described indetail. Referring to the drawings, like numbers indicate like componentsthroughout the views. As used in the description herein and throughoutthe claims that follow, the meaning of “a”, “an”, and “the” includesplural reference unless the context clearly dictates otherwise. Also, asused in the description herein and throughout the claims that follow,the meaning of “in” includes “in” and “on” unless the context clearlydictates otherwise. Moreover, titles or subtitles may be used in thespecification for the convenience of a reader, which shall have noinfluence on the scope of the present invention. Additionally, someterms used in this specification are more specifically defined below.

DEFINITIONS

The terms used in this specification generally have their ordinarymeanings in the art, within the context of the invention, and in thespecific context where each term is used. Certain terms that are used todescribe the invention are discussed below, or elsewhere in thespecification, to provide additional guidance to the practitionerregarding the description of the invention. For convenience, certainterms may be highlighted, for example using italics and/or quotationmarks. The use of highlighting has no influence on the scope and meaningof a term; the scope and meaning of a term is the same, in the samecontext, whether or not it is highlighted. It will be appreciated thatsame thing can be said in more than one way. Consequently, alternativelanguage and synonyms may be used for any one or more of the termsdiscussed herein, nor is any special significance to be placed uponwhether or not a term is elaborated or discussed herein. Synonyms forcertain terms are provided. A recital of one or more synonyms does notexclude the use of other synonyms. The use of examples anywhere in thisspecification including examples of any terms discussed herein isillustrative only, and in no way limits the scope and meaning of theinvention or of any exemplified term. Likewise, the invention is notlimited to various embodiments given in this specification.

Unless otherwise defined, all technical and scientific terms used hereinhave the same meaning as commonly understood by one of ordinary skill inthe art to which this invention pertains. In the case of conflict, thepresent document, including definitions will control.

As used herein, “around”, “about” or “approximately” shall generallymean within 20 percent, preferably within 10 percent, and morepreferably within 5 percent of a given value or range. Numericalquantities given herein are approximate, meaning that the term “around”,“about” or “approximately” can be inferred if not expressly stated.

As used herein, the term “living subject” refers to a human being suchas a patient, or an animal such as a lab testing rat, monkey or thelike.

CNAP is an abbreviation for compound nerve action potential.

CMAP is an abbreviation for compound muscle action potential.

As used herein “target neural tissue” is defined as any neural tissueincluding, but not limited to, the sciatic nerve of the leopard frog(Rana Pepieis), the sciatic nerve of mammals, and brain and spinal cordtissue of mammals.

As used herein “electrical impulse” is defined an electrical currentapplied via electrodes on the nerve to initiate an action potential inthe neuron.

As used herein “stimulation effect” is defined as propagation of anelectrical signal within neural or muscular tissue.

As used herein “nerve fiber” is defined as a portion of the neuron,namely the axon, which carries action potentials from one end of theneuron to the other. Many nerve fibers compose a peripheral nerve, suchas the sciatic nerve of a leopard frog (Rana Pepiens) or a mammal.

Northern Leopard Frog (Rana Pepiens) Sciatic Nerve Model System:

Leopard frogs (Rana Pepiens) provide a widely accepted model system forstudying the stimulation of a neural tissue. The frog sciatic nerveprovides a robust nerve preparation not susceptible to ischemic changes.Additionally, frogs have a neuromuscular innervation similar to mammals,and extensive research has been carried out by the research community onthe ability of neurons to conduct an electrical impulse [48]. Finally,leopard frogs (Rana Pepiens) provide a model system that is capable ofwithstanding temperature and humidity variations [49].

Northern leopard frogs (Rana Pepiens) of sizes varying from 3-4 inchesare selected so that the sciatic nerve may serve as the target neuraltissue. The frogs are pithed so as to euthanize the animal. The frog ispithed to make it brain dead, while still maintaining the vital bodyfunctions and the nerve conduction. Subsequent to being pithed, theanimal is immobilized on a wax bed. The skin covering the hamstringmuscle is cut in order to expose the muscle. Subsequently, an incisionis made along the length of the hamstring muscle so as to expose thesciatic nerve. The sciatic nerve is freed from the connective tissuethat connected it to the surrounding muscle. For experimental purposes,several pairs of electrodes were placed on the nerve. The first pair ofelectrodes is capable of electrical stimulation, the second pair ofelectrodes is capable of recording the nerve potentials, and the thirdpair of electrodes was pierced into the muscle that the sciatic nerveinnervates so that muscle potentials may be recorded. Additionally, thesciatic nerve was kept moist at all times by using saline water.

The methods described herein may have been used to stimulate a ratsciatic nerve. One of ordinary skill in the art understands thedifferences in the surgical procedure necessary to expose the ratsciatic nerve compared to the surgical procedure described above for thefrog. The same method of optical stimulation was used for the rat nerveand frog nerve. Regarding the stimulation of the rat sciatic nerve, awavelength of 4.4 micrometers, and energy of 4.7 mJ, a spot size of 619micrometers, and a pulse frequency of 2 Hz using the FEL were used.Optical stimulation was also tested using an energy of 39 mJ, 1.78 mJ,or 2.39 mJ.

Free Electron Laser (FEL):

A free electron laser and delivery optics are used to generate andmanipulate the optical energy. The optical energy transport system ismaintained under rough vacuum. The optical energy is focused on thetarget neural tissue using focusing lenses (Vi Convex Lenses, f=300 mm)to a spot size of around 400 micrometers.

The response of the sciatic nerve to the optical energy stimulation issensed using stainless steel needle electrodes that are placed under thesciatic nerve for compound nerve action potential recording.Additionally, the electrical response from the sciatic nerve ismonitored by recording electrodes placed in the nerve downstream andinnervated hamstring muscle. If the sciatic nerve conducts an electricalimpulse, a tiny electrical signal can be detected from the nerve (CNAP)and a much larger electrical signal can be detected from the muscle(CMAP). The signals are recorded using the MP100 system from BiopacSystems (Santa Barbara, Calif.) that is combined electrical stimulationand recording unit. The nerve was electrically stimulated using S44Grass electrical stimulator from Grass Instruments, Quincy, Mass.

Optical stimulation was performed using laser pulses with energy in therange from 0.2 mJ to 5 mJ with a spot size of 300-600 micrometers(fluence values varied from 0.2 J/cm² to about 10 J/cm²). The minimumenergy and therefore fluence required to stimulate the frog nerve wasfound to be minimum (0.6 J/cm²) between 4 and 4.5 micrometers. The spotsize of the optical energy was determined using the knife-edge method[50]. The laser pulses were focused onto the sciatic nerve usingBiconvex Lenses. The laser pulse energy was varied using a polarizer.The information recorded on the MP100 system was displayed using theAcqKnowledge software.

The FEL was selected for use in the initial studies with this methodsince it has the following advantages. The FEL is tunable in wavelengthfrom 2 to 10 micrometers. Thus, FEL offers the flexibility of providingvarious wavelengths in the infrared spectrum for use with the methodprovided herein. Other sources may be used to generate the necessarywavelength. In addition to any source that can generate wavelengths inthe infrared portion of the spectrum, sources may include LED and LCD.FEL additionally provides micropulses, each about 1 picosecond induration and having a repetition rate of about 3 GHz. The envelope ofthis pulse train forms a macropulse that is about 3-6 microseconds andcan be delivered at a rate up to 30 Hz. As mentioned above, opticalstimulation of the peripheral nerves employ pulse energies ranging from0.2 mJ to 5 mJ in a spot size of around 500 micrometers.

Stimulation studies can also be performed using other sources such as aYAG laser for wavelengths in the UV, visible and infrared. Additionally,if it is desired to use a wavelength around 4 micrometers, then alead-salt laser, or an optical parametric oscillator (or amplifier) maybe used.

OVERVIEW OF THE INVENTION

Recently, it has been demonstrated by the inventors a fundamentallynovel device for neural activation using low-level, pulsed infraredlaser energy in vivo with resulting compound nerve and muscle potentialsand associated muscle contraction. It is also shown that infrared laserlight incorporated into a stimulation device at 4.0 and 2.1 μm can beused to consistently and reproducibly stimulate peripheral nerves infrogs and rats with no appreciable tissue damage using radiantexposures, laser energy per unit area, of 1.01 and 0.32 J/cm²,respectively; 4-6 times below an ablation (damage) threshold. The ratioof the ablation threshold to a stimulation threshold (safety ratio) isfound to be inversely proportional to the tissue absorption and thisratio is highest at relative valleys of tissue absorption in theinfrared. Histological analysis shows no discernable tissue damage withchronic stimulation. These results prove that optical stimulation cancircumvent many of the limitations of electrical stimulation, includinglack of spatial specificity and electrical artifacts. The resultingnerve and muscle action potentials recorded are analogous to thatobserved with electrical stimulation. The pulsed, laser irradiation froma laser device can be focused to a small diffraction limited spot with ahigh degree of precision, thereby targeting specific neural fibers andfacilitating spatial selectivity of neural response that is notattainable with electrical stimulation in vivo.

The present invention, among other things, discloses methods and systemsfor facilitation and/or enhancement of the optical stimulation of neuraltissues, with the use of exogenous chromophores, endogenous chromophoresand/or optical agents. In one embodiment, the method includes the stepsof generating at least one beam of radiation; introducing at least oneof one or more chromophores and one or more optical agents to a targetneural tissue; and delivering the at least one beam of radiation to thetarget neural tissue, where the at least one beam of radiation isdelivered with a radiant exposure that causes a thermal gradient in thetarget neural tissue, thereby stimulating the target neural tissue. Theexogenous agents may be external to the neurons and/or be loaded intothe intracellular space, so long as the agents act to enhance theunderlying mechanism of optical stimulation through a thermally mediatedprocess and/or directly facilitate this optical stimulation of neuraltissue using a chromophore normally not present in tissue to directlycause the thermally mediated mechanism by which pulsed laser stimulationoccurs. Similarly, endogenous chromophores can be targeted near the cellmembrane to cause efficient stimulation without significant absorption(i.e., heat generation) from surrounding tissues.

The at least one beam of radiation has an intensity between a firstintensity threshold and a second intensity threshold that is greaterthan the first intensity threshold, wherein the first intensitythreshold is a stimulation threshold of the target tissue, and whereinthe second intensity threshold is an ablation threshold of the targettissue. The ratio of the second intensity threshold to the firstintensity threshold is a function of a wavelength of the at least onebeam of radiation. In one embodiment, the ratio of the second intensitythreshold to the first intensity threshold is in a range from 1 to 200,preferably in a range from 4 to 6. The at least one beam of radiation isdelivered to the target neural tissue with the radiant exposure no morethan 5.0 J/cm², preferably no more than 2.0 J/cm². The at least one beamof radiation has a plurality of pulses with a pulse duration, T_(p),less than a thermal diffusion time, T_(d), of the target neural tissue.

Results demonstrate that efficient optical stimulation wavelengthsmirror the tissue absorption spectrum, thus all wavelengths in the IRare capable of stimulation, however, optimal wavelengths do exist thatare based on the depth of absorbed pulsed light in tissue. This suggeststhat the intrinsic tissue absorption properties are primarilyresponsible for efficient stimulation with minimal tissue damage.

The mechanism of action for this phenomenon is related to establishing athermal gradient in the tissue (at the level of the neuronal cellmembrane) that causes subsequent stimulation due to the increase intemperature. Furthermore, theoretically with the addition of exogenouschromophores in the target tissue, the absorption can be changed basedon the material properties of that deposited enhancer. These propertiesmay be optimized to not only absorb light efficiently (thus establishthe thermal gradient in tissue) at the appropriate energy levels, butalso act as a heat sync to minimize thermal damage in tissue associatedwith this nerve stimulation phenomenon. With this known thermalmechanism for stimulation of neural tissue, any wavelength of light canbe used for stimulation, provided the light is absorbed by the opticalenhancing medium and transferred to heat locally near the cell membrane.An optimal wavelength for use of an exogenous chromophore would be onethat has minimal absorption in neural tissue, yet optimal absorption(i.e. absorption that is higher than that of the tissue) in theenhancing material. The optimal wavelength for stimulation with anendogenous chromophore would be one that localizes the thermal gradientnear the cell membrane without significant absorption from other tissuelayers. This known mechanism of action will certainly improve the methodof optical stimulation in neural tissue by maximizing efficiency of thephenomenon while at the same time minimizing damage to the tissue.

Theoretically, with the addition of exogenous chromophores in the targettissue, the absorption can be changed based on the material propertiesof that deposited enhancer. These properties may be optimized to notonly absorb light efficiently at the appropriate energy levels, but alsoact as a heat sink to minimize thermal damage in tissue associated withthis nerve stimulation phenomenon. Furthermore, any wavelength of lightcan be used for stimulation, provided the light is absorbed by theoptical enhancing medium. An optimal wavelength for this phenomenonwould be one that has minimal absorption in neural tissue, yet optimalabsorption (i.e. absorption that is higher than that of the tissue) inthe enhancing material. This certainly improves the method of opticalstimulation in neural tissue by maximizing efficiency of the phenomenonwhile at the same time minimizing damage to the tissue.

In one embodiment, experiments using a pulsed alexandrite laser (750 nm)were performed to validate this novel idea on the rat sciatic nerve invivo. The alexandrite laser operates at a wavelength that has minimalabsorption in soft tissue, including neural tissue. Optical stimulationdoes not occur with low levels of energy incident on neural tissue usingthis laser. However, by increasing the energy to over 200 times thatrequired for optical stimulation using the optimal wavelength at 2.12microns, the tissue began to dehydrate and carbonize. With this changein tissue properties, the tissue absorption coefficient increasessignificantly. Upon inflicting this change in the tissue properties,stimulation threshold over this area therein was significantly reduced.This was the first experiment to demonstrate that a change in absorptionproperties in nerve tissue may facilitate optical stimulation with aminimally absorbed laser beam.

The biophysical mechanism of the optical stimulation of the neuraltissue was further analyzed by careful examination of possiblephotobiological effects following absorption driven light-tissueinteraction. Specifically, a sciatic nerve was stimulated in vivo withthe Holmium:YAG laser (2.12 μm), Free Electron Laser (2.1 μm),Alexandrite laser (690 nm), and the commercial prototype solid statelaser nerve stimulator built by Aculight (1.87 μm), respectively.Through a process of elimination approach, relative contributions to theoptical stimulation were determined from interaction types resulting inthe optical stimulation, including temperature, pressure, electricfield, and photochemistry. It is demonstrated that neural activationwith pulsed laser-light occurs by a transient thermally inducedmechanism. Data collected reveal that the spatial and temporal nature ofthis temperature rise, including a measured surface temperature changerequired for stimulation of the peripheral nerve (7-10° C.). Thisinteraction is a photo-thermal effect from transient tissue temperaturechanges, a temperature gradient at the axon level (4.5-6.4° C.),resulting in direct or indirect activation of transmembrane ion channelscausing action potential propagation. Stimulation requires that theincrease in temperature occur before significant thermal diffusion canoccur. Therefore, the laser pulse duration must be significantly lessthat the thermal diffusion time in the specific neural tissue type (atissue property). In the case of the peripheral nerve, this is roughly5-10 msec. It is shown that an exogenous chromophore introduced to anerve tissue can be used to directly facilitate the stimulation in awavelength otherwise not absorbed by the nerve tissue, by leading tonerve activation and action potential propagation. Preferably, thechromophores (exogenous or endogenous) is one that maximizes temperatureincreases while minimizing tissue damage in the target neural tissue.

The method according to the present invention has advantages over theexisting optical neural stimulation methodology by: 1) increasingspatial resolution to only the area where exogenous chromophore isloaded or placed, 2) increasing the number of lasers and wavelengthsavailable for optical stimulation by changing the absorption propertiesof the target tissue (thus allowing stimulation), 3) enhancing existingoptimal wavelengths to decrease the amount of laser energy required forstimulation as well as possibly increasing the energy required fortissue damage by acting as a heat sync in the nerve, 4) allowing thepossibility of non-invasive stimulation by coating/loading the targetneurons prior to stimulation and the use of a laser with a wavelengththat is both capable of penetrating soft tissue as well as being highlyabsorbed by the input chromophore.

Referring to FIG. 1, a system 100 for optically stimulating a neuraltissue (sciatic nerve) is shown according to one embodiment of thepresent invention. The system 100 has an energy source 110 forgenerating optical energy. The energy source 110 in this embodimentincludes a Holmium:YAG laser. The energy source 110 can also be a freeelectron laser, an Alexandrite laser, a solid state laser, a CO₂ laser,a tunable OPO laser system, an N₂ laser, an excimer laser, or an Er:YAGlaser, or the like.

The optical energy in the embodiment is generated in the form of a beamof pulsed IR light 120 along a first optical path 121. The beam ofpulsed IR light 120 has pulses with a pulse duration T_(p) that is lessthan a thermal diffusion time, T_(d) of the sciatic nerve 190.

In operation the optical energy is delivered to a sciatic nerve 190 by adelivering means that optically coupled to the optical source 110. Thedelivering means is configured to deliver the optical energy with aradiant exposure that causes a thermal gradient in the sciatic nerve190, so as to stimulate the sciatic nerve 190. In this embodiment, thedelivering means includes a mirror 130, a focusing lens 140, a coupler150, an optical fiber 160 coupled to the coupler 150 and a probe 170coupled to the optical fiber 160. The mirror 130 is placed between theenergy source 110 and the focusing lens 140 along the optical opticalpath 121 of the beam of pulsed IR light 120 for transmitting a portion123 of the beam of pulsed IR light 120 to the focusing lens 140 alongthe first optical path 121 and reflecting the remaining portion 124 ofthe pulsed IR light 120 to an energy detector 183 along a second opticalpath 122 that is perpendicular to the first optical path 121. Theportion 123 of the beam of pulsed IR light 120 transmitted to thefocusing lens 140 is focused onto the coupler 150 and is then deliveredthrough the optical fiber 160 and the probe 170 to the sciatic nerve 190for optical stimulation thereof. The optical energy delivered to thesciatic nerve 190 can be determined by measuring the optical energy ofthe remaining portion 124 of the pulsed IR light 120 by the energydetector 183.

Additionally, the delivering means may also include a movable stage (notshown) that is operably coupled to the probe 170 such that the probe 170is movable with the movable stage three-dimensionally to selectivelydeliver the optical energy to one or more neural fibers of the sciaticnerve 190.

As shown in FIG. 1, the system 100 also includes an IR mirror 181 and anIR FPA camera 182 positioned in relation to the sciatic nerve 190 formonitoring the temperature profile (i.e., the thermal gradient) of thesciatic nerve 190 caused by the optical energy delivered from the probe170. The monitored temperature profile of the sciatic nerve 190 istransmitted to a computer 184 for evaluation and/or display of theoptical stimulation of the sciatic nerve 190. In addition, the system110 also has a trigger 185 coupled between the energy source 110 and thecomputer 184 for activating and/or controlling the output (intensityand/or wavelength) of the Holmium:YAG laser 110 based on the evaluationof the optical stimulation monitored by the IR FPA camera 182.

These and other aspects of the present invention are more specificallydescribed below.

IMPLEMENTATIONS AND EXAMPLES OF THE INVENTION

Without intent to limit the scope of the invention, exemplary methodsand their related results according to the embodiments of the presentinvention are given below. Note that titles or subtitles may be used inthe examples for convenience of a reader, which in no way should limitthe scope of the invention. Moreover, certain theories are proposed anddisclosed herein; however, in no way they, whether they are right orwrong, should limit the scope of the invention so long as the inventionis practiced according to the invention without regard for anyparticular theory or scheme of action.

Several exemplary experiments were conducted at the VanderbiltUniversity W. M. Keck Free Electron Laser Center and the VanderbiltBiomedical Optics Laboratory in accordance with animal protocolsapproved by the Institutional Animal Care and Use Committee (IACUC).

Example Biophysical Mechanism Responsible for Low-Level, TransientOptical Stimulation of Peripheral Nerve

In vivo neural activation with low-levels of pulsed infrared light [1]exhibits advantages over standard electrical means by providing acontact-free, spatially selective, artifact-free stimulation method [2]that encourages development towards clinical application. In thisexample, the biophysical mechanism underlying this phenomenon wasdetermined by careful examination of possible photobiological effectsfollowing absorption driven light-tissue interaction. Sciatic nervepreparation was stimulated in vivo with the Holmium:YAG laser (2.12 μm),Free Electron Laser (2.1 μm), Alexandrite laser (690 nm), and thecommercial prototype solid state laser nerve stimulator built byAculight (1.87 μm), respectively. Through a process of eliminationapproach, relative contributions to the neural activation weresystematically determined from interaction types resulting in opticalstimulation, including temperature, pressure, electric field, andphotochemistry. Collectively, the results imply neural activation withpulsed laser-light occurs by a transient thermally induced mechanism.Data collected reveal that the spatial and temporal nature of thistemperature rise, including a measured surface temperature changerequired for stimulation of the peripheral nerve (7-10° C.). Thisinteraction is a photo-thermal effect from transient tissue temperaturechanges, a temperature gradient at the axon level (4.5-6.4° C.),resulting in direct or indirect activation of transmembrane ion channelscausing action potential propagation.

Methods

All experiments were conducted at the Vanderbilt University W. M. KeckFree Electron Laser Center and Vanderbilt Biomedical Optics Laboratoryin accordance with standards set by the Institutional Animal Care andUse Committee.

A. Animal Preparation (Rat and Frog):

Spraque-Dawley rats (300 to 400 g) were implemented for theseexperiments. In preparation for surgery, 60 rats and 4 frogs wereanesthetized with IP injection of ketamine (80 mg/kg) and xylazine (10mg/kg) solution and maintained under sedative with additional boluses ofketamine for the duration of individual experiments. Once anesthetized,animals were placed in the prone position and the right and left sciaticnerve exposed over the length of the femur. An incision was madeposterior-laterally extending from the gluteus muscles to the poplitealregion. This allowed access to the sciatic nerve from its exit from thepelvic cavity to the level of the knee and allows for visualization ofspecific motor branches (n. fibularis and n. tibialis) to the bicepsfemoris, gastrocnemius, and distal muscles. The muscle fascia overlyingthe nerve was carefully removed to expose the nerve surface with itsepineurial (outer) covering maintained intact. Nerves were continuallymoistened with normal saline to avoid desiccation during the acutestudy.

B. Experimental Design and Electrophysiological Evaluation:

Each nerve tested was set up such that optical stimulation could beperformed at a point adequately proximal to recording electrodes in themain trunk of the sciatic nerve. Furthermore, a motor branch of thesciatic nerve leading to the biceps femoris muscle was easily identifiedand allowed observation upon stimulation of motor fibers in the sciaticnerve. Recordings of compound nerve action potentials (CNAPs) were madeby placing a bipolar electrode under the nerve at one or two pointsdistal to the point of stimulation. Compound muscle action potential(CMAP) recordings were made by placing needle electrodes (Grass E-2electrodes; Grass Telefactor, Inc.; West Warwick, R.I.) into the musclebelly in a bipolar fashion (belly-to-belly placement). Responses wererecorded with a modular data acquisition system (MP100, Biopac SystemsInc. Santa Barbara, Calif.) controlled using a laptop computer andAcknowledge® software (Biopac Systems Inc.). For the purposes of thisstudy, stimulation threshold was defined as the minimum radiant exposureincident on the peripheral nerve surface required for one visible muscletwitch per laser pulse. Recorded responses served to confirm the evokedstimulation and nerve potential propagation.

C. Laser Setup (Holmium, Alexandrite, Aculight):

Tissue morphology and optical properties determine the distribution anddepth of penetration of light energy and the potential for bothexcitation and damage to the laser irradiated nerve. The literatureprovides evidence that laser light at 2.1 μm wavelength is optimal forstimulation in the rat peripheral nerve [2]. A portable Holmium:YAGlaser (Ho:YAG Model 1-2-3 laser, Schwartz Electro Optics, Inc.) was usedin many of these studies. This laser operates at a wavelength of 2.12 μmwith pulse duration of 350 μs (Full Width Half Maximum—FWHM). The Ho:YAGlaser beam is coupled directly to a 600 μm optical fiber (3M OpticalFiber Power Core, FT-600-DMT), which was mounted on a three dimensionalmicromanipulator and precisely positioned over the nerve at theidentical site of electrical stimulation. The intensity of radiantexposure (0.3-1.0 J/cm²) was controlled via attenuating optical filters.Reported radiant exposures were calculated based on the spot size at thetissue; given the optical fiber diameter, the distance from fiber totissue, and the numerical aperture of the fiber. Alternately, a FreeElectron Laser (2-10 μm) located at Vanderbilt University was tuned to2.1 μm for pulse duration studies, as well as the first generation of asolid state diode laser device for optical nerve stimulator made byAculight (Bothel, Wash.) operating at 1.87 μm. Finally, an Alexandritelaser crystal was used for an additional study to examine the effect ofa laser induced electric field on nerve stimulation by changing thecrystal within the Schwartz Electro Optics 1-2-3 laser to output awavelength of 750 nm while all other laser parameters remainedunchanged.

D. OCT Measurements:

Surface displacement attributable to pressure transients accompanyingthermoelastic expansion upon laser irradiation were measured using adifferential phase optical coherence tomography (DP-OCT) system from UTAustin [19-21]. This system was employed to make use of its extremelyhigh spatial and temporal resolution measurement capabilities. Ratsciatic nerve tissue was placed in a petri dish hydrated with saline andcovered with a thin microscope slide coverslip for ex vivo experiments.The Ho:YAG laser coupled to a 600 μm fiber located 0.75 mm from thetissue was used to irradiate the tissue over a range of radiantexposures (0.3 to 1.0 J/cm²). Differences in fringe signals from thesurface of the nerve tissue relative to the overlying coverslip(reference position) allowed real time measurement of the surfacedisplacement following each laser pulse with a spatial resolution of 20nm sampled at 1 MHz. An optical trigger facilitated synchronousrecording of the exact timing of pulse delivery for all experiments.

E. Piezoelectric Experiments:

The prospect of pulsed stress waves leading to a stimulatory effect inneural tissue was investigated in vivo with a custom made mechanicalpiezoelectric element. A piezo actuator (NA-09 Piezo Actuator, DSM,Franklin, Tenn.) with a 9 micron range rated for a total voltage rangeof −30/+120 V was designed and assembled into a structure (3×1×1 cm)with a mounting base and location for an output tip. The removablethreaded tip insert consisted of a 1 mm diameter fabricated ceramicsphere oriented in the direction of motion of the actuator. This tipdesign mimicked the shape and size of a Gaussian shaped Ho:YAG laserbeam from a 600 micron fiber located 0.75 mm from the target tissue justat the surface of the irradiated nerve. The actuator's open loopdisplacement versus applied voltage was characterized to produce aconstant velocity move based on DP-OCT data collected regarding surfacedisplacement using threshold radiant exposures with the Ho:YAG laser (atleast 300 nm in 350 microseconds). The actuator was connected to alinear amplifier (VF-2000, DSM, Franklin, Tenn.) with an input voltagegain of 21.3. The entire system was computer controlled by a softwareprogram (Labview, National Instruments, Austin, Tex.). Triangle andsinusoidal input waves corresponding to an increase and decrease inactuator position allowed for fast pressure transients to be deliveredto the surface of the sciatic nerve in vivo. CNAP and CMAP recordingswere triggered from the onset of actuator motion to observe anystimulatory effect from expansion and compression waves. The range ofdisplacement amplitudes used paralleled measurements of thermoelasticexpansion and the time for the total displacement was held at 350 μsec,the length of the Ho:YAG laser pulse.

F. Cold Frog Experiments:

Experiments in frog sciatic nerve examined the temperature dependence ofstimulation threshold. The frog was chosen as the best model for theseexperiments due to its cold blooded nature, and ability to maintainnerve conduction over a wide temperature range. To determine temperaturevalues of the bath, a wire thermocouple (Type E, Chromel/Constantin,Omega Engineering Inc., Stamford, Conn.) was suspended in the fluid andtemperature values were recorded at a rate of 500 Hz using a dataacquisition system (Labview, National Instruments, Austin, Tex.) Thenerve and optical fiber were submerged in saline maintained attemperatures of 0 and 25° C. Time between trials (10 minutes) allowedfor adequate heat diffusion to tissue and thus this study assumes thetemperature of the bath and the tissue is identical. This also helpedminimize tissue dehydration, which can drastically affect thestimulation threshold. A 600 μm fiber coupled to the Ho:YAG laser wasplaced 0.4 mm from the nerve surface and stimulation thresholds recordedfor 3 trials at each temperature for each nerve (n=6).

G. Two Dimensional Radiometry of Irradiate Tissue Surface:

Two dimensional radiometry was used to observe the irradiated tissuesurface temperature profile in both time and space. FIG. 1 illustratesthe Indigo Systems infrared (thermal) camera with Phoenix dataacquisition system, located in UT Austin [22], used for gatheringtemperature profiles in vivo upon Holmium:YAG laser stimulation of therat sciatic nerve at 2 Hz. A 600 μm fiber was coupled to the laser andheld at a constant distance of 0.5 mm from the tissue during all trials.Recordings were taken for 1 second at a sampling rate of 800 kHz.Temperature data was normalized and output as a function of time andposition (x, y). Measurements of the surface temperature of the nerve inthe two dimensional plane (10 cm×2.5 cm FOV) were observed both duringand after the laser pulse. Measurements using a range of radiantexposures from stimulation threshold to radiant exposures causingthermal changes in tissue (0.3-0.9 J/cm²) were conducted in hydratednerve tissue (n=18).

Results

A. Electric Field:

Maxwell's EM theory suggests an inherent electric field exists withinlaser light, which is associated with the propagation of light itselfand driven by time and space varying electric and magnetic fields [23].Since the conventional method uses electricity to excite axons,questions arise whether the electric field within the incident lightbeam is large enough to directly initiate action potentials. Considerthe following equation:

S _(threshold)=½cε _(o) E _(max) ²,  (1)

where threshold laser radiant exposure (S_(threshold))=0.32 J/cm² withthe Ho:YAG laser, the speed of light (c)=3e¹⁰ cm/sec, permittivity ofneural tissue (ε_(o)) (cε_(o)=0.002634 A-s/V-m)[24]. The calculatedtheoretical value for the maximum instantaneous intensity of theelectric field (E_(max)) at the tissue surface is 0.155 V/mm².

The Alexandrite laser operating at 750 nm (red light) was used toattempt stimulation of the peripheral nerve. The Ho:YAG laser crystaland mirrors typically used for optical stimulation experiments werereplaced with the Alexandrite crystal and mirrors. In this setup laserparameters and beam characteristics remained constant (i.e. pulseduration, fiber size, spot size, repetition rate, and electric fieldstrength) except wavelength, which changed from a fairly high absorption(Ho:YAG, μ_(a)=333 μm) to a very low absorption (Alexandrite, μ_(a)=10⁶μm) in soft biological tissue. A total of 4 nerves were irradiatedthrough a range of radiant exposures from stimulation threshold to thosecausing thermal changes in the tissue (0.3 J/cm² to 51.7 J/cm²). TheAlexandrite laser did not stimulate the peripheral nerve in any trialusing radiant exposures up to 150 times Ho:YAG stimulation threshold. Asa side note, these results provide experimental evidence that the laserelectric field does not stimulate neural tissue. However, upon tissuedehydration and carbonization using radiant exposures greater than 50J/cm² the laser was able to repeatedly stimulate the nerve.

B. Photomechanical:

This study examined plausible photomechanical effects leading to opticalstimulation; namely thermoelastic expansion or pressure wave generationfrom rapid heating. Contributions from pressure waves to opticallystimulate the peripheral nerve were studied by observing the effect ofvarying pulse duration on stimulation threshold. FIG. 2 depicts theeffect of varying pulse width on the minimum incident radiant exposurerequired for an action potential using three lasers with nearlyequivalent absorption coefficients, or depths of penetration rangingfrom 333 to 450 μm; the FEL (2.1 μm, 5 μs), Ho:YAG (2.12 μm, 350 μs),and tunable solid state Aculight laser (1.87 μm, 1-5 msec). Hence,stimulation threshold was established for 5 different pulse durations (5μsec, 350 μsec, 1 msec, 3 msec, 5 msec) for 10 trials each. It is clearfrom this figure that the threshold radiant exposure required forstimulation at this tissue absorption does not significantly change withvariable pulse width through almost 3 orders of magnitude, includingthose pulse durations that lie well outside of the stress confinementzone. These data along with an understanding of photomechanicalinteractions directly contradict the notion that pressure wavesgenerated from rapid heating are responsible for optical nervestimulation. This idea is discussed in detail within the discussionsection.

The next set of experiments focused on mechanical stimulation fromthermoelastic expansion in tissue upon tissue absorption and subsequentheating by internal conversion. It is very difficult, if not impossible,to design in vivo optical stimulation experiments that decoupletemperature rise and associated pressure transients. In a set ofshrewdly designed experiments the thermoelastic expansion of the nervesurface was measured over the typical range of radiant exposuresrequired for peripheral nerve excitation. Results helped characterizethe amplitude of mechanical pressure waves, which were injected into thetissue in a second series of experiments. Thus, the thermal andmechanical effects were disassociated so that the mechanical effectswithin the nerve from thermoelastic expansion could be observedindependently.

Tissue displacement during the laser pulse was measured using a phasesensitive OCT setup from UT Austin [20] to test the actual magnitude oftissue thermoelastic expansion from optical stimulation. The typicalnerve displacement in time measured from this system during a singlelaser pulse is seen in FIG. 3 a. Notice the rapid increase in opticalpath length change and exponential decay of the waveform. This maximumvalue corresponds to immediate absorption, heating and maximumthermoelastic expansion resulting from the laser pulse. Note in theexample that the time required for the maximum displacement to occur is350 μsec, the pulse width of the Ho:YAG laser. The exponential decay indisplacement represents the typical thermal decay in tissue based on thethermal diffusion time, a tissue property. FIG. 3 b describes themaximum change in surface displacement of 3 rat sciatic nerves (ex vivo)upon irradiation with Ho:YAG laser over the typical physiologic range ofradiant exposures for optical stimulation. As expected, displacementincreases linearly with laser radiant exposure, theoretically supportedby the following equation:

ΔP=(1/γ)(ΔV/V)*ΔT,  (2)

where the change in pressure (ΔP) is linearly proportional to the changein temperature (ΔT) and related by the product of the inverse of thecoefficient of isothermal compressibility (γ in units [Pa⁻¹]) and theratio of the change in volume (ΔV) over the total irradiated volume (V).Surface displacement slightly above threshold (0.4 J/cm²) was measuredto be 300 nm. Hill et al reported membrane displacement measurements of1.8 nm from the normal physiologic rapid change in cell diameter incrayfish giant axons following electrical stimulation [25]. Thus while adisplacement of 300 nm in a 350 μsec pulse width is very small thisvalue can not be considered negligible since it is much greater thanrapid displacements experienced by the typical axon.

Quantitative data on the exact amplitude and duration of the pressuretransients secondary to tissue temperature changes from pulsed laserirradiation provided the framework for the design of a piezoelectricactuator that mimics beam characteristics in optical stimulation.Similarly between spot size of the typical laser beam used in DP-OCTexperiments and actuator tip helped normalize the effective tissuevolume changes upon tissue displacement (see Equation 2). In theexample, pressure transients are extricated from temperature increasesto examine the effect, if any, from simulated photomechanicalstimulation of the peripheral nerve. For these studies a variety ofmechanical pulse wave shapes and amplitudes were delivered to a total of10 rats (20 nerves). For each nerve, both triangle and sinusoidal shapedwaveforms varying in amplitude from 300 nm to 9 microns were deliverednormal to the surface of the nerve via the beam shaped actuator tip.Based on displacement measurements, the maximum temperature rise occurs350 μsec after onset of the laser pulse (the pulse width of the Ho:YAG).Compression and expansion waveforms were delivered in this 350 μsec timecourse for all experiments. Results reveal that pressure transientsdelivered to the nerve surface in a manner analogous to laser inducedthermoelastic expansion waves are not capable of initiating actionpotentials with amplitudes at least 30 times those measured for opticalnerve stimulation threshold.

C. Photothermal:

To provide compelling evidence for a photothermally mediated mechanism,the effect of pulse width changes on the onset time for stimulation andaction potential propagation was observed. CNAP's were recorded exactly6 mm distal to the site of rat peripheral nerve stimulation upon opticalstimulation from Aculight's portable optical nerve stimulator (1.85 μm).The tunable pulse width was employed to observe changes in the onsettime for the action potential with variable laser pulse durations. FIG.4 depicts the recorded CNAP's from identical stimulation and recordingsites in one nerve using 2.5 msec and 8.0 msec laser pulse lengths(shaded rectangles), all additional laser parameters were constant foreach trial. Laser radiant exposure was held constant and slightly abovethreshold for each recording (0.4 J/cm²) as indicated by the similaramplitudes of peak CNAP. It is reasonable to assume that the conductionvelocities for the recordings in FIGS. 4 a and 4 b are identical becausesimilar motor axons were recruited for each trial, yielding a conductiontime for both CNAP's of 2.6 msec. The most notable observation from thisstudy is that the onset time for stimulation varies with width of thelaser pulse. This implies that all laser energy must be deposited in thetissue before action potential propagation can occur.

A study was performed to detect changes in onset time of the CNAPresponse upon optical stimulation with varying laser radiant exposure toaugment understanding of mechanistic contributions based on temperature.FIG. 5 depicts CNAP recordings stimulated (t=0) with a 6 msec pulsewidth using the tunable pulse Aculight optical nerve stimulator. CNAP'swere recorded 4 mm from the stimulation site for each recording, shownin FIG. 5 a. All experimental variables and laser parameters were heldconstant during stimulation and recording of FIGS. 5 b and 5 c, with theexception of the laser radiant exposure, 0.6 J/cm2 and 1.2 J/cm2,respectively. The onset time of the response in FIG. 5 b is 7.8 msecfollowing the laser pulse and 4.8 msec for FIG. 5 c. Again a constantconduction time for both recordings was assumed (1.8 msec). It is clearfrom these traces that as the optical energy used for stimulation isincreased, the onset time for the CNAP occurs in a shorter time.

The effect of nerve tissue temperature on the threshold radiant exposurerequired for stimulation was determined. The cold blooded amphibiannerve temperature was manipulated in a saline bath in vivo to facilitatenerve stimulation at temperatures of 0 and 25° C. Time between trials(10 minutes) allowed for adequate heat diffusion from bath to tissue andthus this study assumes the temperature of the bath and the tissue isidentical. Both the optical fiber for stimulation and the peripheralnerve were submerged in the temperature controlled saline solution andheld at a distance 0.4 mm away. This caused the reported thresholdradiant exposures for stimulation to increase as the saline between thefiber and tissue absorbed much of the optical energy. Since this is acomparative study all experimental parameters remained unchanged foreach trial to normalize collected threshold data. Stimulation thresholdaverages at 25° C. were 0.91 and 0.84 J/cm² for the two frogs studiedwith 3 trials for each nerve (n=6). Similarly, average thresholds forstimulation at 0° C. were 1.01 and 0.86 J/cm², (n=6) respectively. Theseresults indicate no significant change in threshold occurs with changesin nerve tissue temperature.

Photothermal effects result from the transformation of absorbed lightenergy to heat, which may lead to coagulation or ablation of the targettissue depending on tissue optical properties and laser radiantexposure. Two-dimensional radiometry of the irradiated tissue surfacewas performed to gain a better understanding of the thermal processesand actual tissue temperature values required for optical nervestimulation. Using this technique, the temperature profile in space andtime were observed following Ho:YAG laser stimulation. FIG. 4 containsthe surface temperature profile (x, y) of the single frame containingthe maximum temperature value recorded for all frames (800 frames in 1sec recording) irradiating the nerve with threshold radiant exposure(0.4 J/cm²). This corresponds to the first frame in which all laserenergy has been deposited in the nerve tissue. The two graphs belowcontain the temperature profile for the column (right) and row (left)containing the maximum temperature pixel. The solid lines represent thebest Gaussian fit for each temperature profile in space. Peak tissuetemperature for this trial upon optical nerve stimulation in vivo (wellhydrated tissue) was measured to be 35.86° C. This is a peak temperaturerise of 8.95° C., yielding an average temperature rise across theGaussian laser spot of 3.66° C. with radiant exposures near stimulationthreshold. This is very close to the theoretically calculated averagetemperature rise for a uniform beam with the same laser parameters andneglecting scattering equal to 2.87° C.

Thermal measurements of the rat sciatic nerve surface (n=18) were takenin vivo for each nerve using a range of radiant exposures from 0.3-0.9J/cm² in well hydrated tissue. FIG. 7 a represents the data collectedfor the maximum surface temperature for a single trial (diamonds) andpeak temperature rise in tissue (squares) immediately following laserstimulation as a function of radiant exposure. FIG. 7 b describes theaverage thermal gradient, temperature rise from baseline, as a functionof laser radiant exposure for all trials (n=18). Clearly, nervetemperature increases linearly with laser radiant exposure. Resultspredict the minimum temperature increase of the nerve surface requiredfor stimulation (0.3-0.4 J/cm²) is as low as 6° C., yielding a peaktemperature of 31° C., provided that the laser pulse width issufficiently short (<10 msec). Minimum temperatures for onset ofthermally induced changes in mitochondria function and proteindenaturation are shown in FIG. 7 a. In the case of non-hydrated tissue(data not shown), the temperature as a function of radiant exposureshifts upward due to a difference in optical properties compared withhigher water content tissue. In the example, the mitochondrial damagewill theoretically begin to occur between 0.5-0.6 J/cm²; thusillustrating the importance of tissue hydration for safer, moreefficient nerve excitation.

The peripheral nerve temperature profile in time was also observed usingthe infrared camera. Results from Ho:YAG laser stimulation slightlyabove threshold (0.4 J/cm²) and at two times threshold radiant exposure(0.8 J/cm²) are shown in FIG. 8. These graphs provide the peaktemperature at the height of the Gaussian spatial profile for each framein time following a single laser pulse at t=0. The exponential decreaseof temperature in time represents a typical thermal decay in the nervetissue. Thermal relaxation time (i.e. the time to dissipate heatabsorbed from a laser pulse) is defined as the time for the temperatureof the tissue to return to 1/e (37%) of the maximum tissue temperaturechange. In the case of the rat peripheral nerve, as shown in FIG. 8, thethermal relaxation time was estimated to be about 90 msec. Notice thatthe thermal relaxation time is independent from laser radiant exposure.Temperature superposition, or additive temperature effects from multiplepulses, was observed for a period of 5 seconds using 2 Hz and 5 Hzstimulation frequencies. These results are shown in FIG. 9. It is clearthat the temperature increase and return to baseline tissue temperatureis consistent upon multiple laser pulses with a frequency of 2 Hzregardless of laser radiant exposure. This demonstrates that there areno additive temperature effects in peripheral nerve tissue with lowfrequency stimulation near threshold. A frequency of 5 Hz does havetemperature superposition effects as the tissue temperature increasedoes not return to baseline prior to absorption and heating from thenext pulse in the sequence. This quickly leads to a much larger maximumtemperature in the tissue than seen with 2 Hz stimulation. The largerradiant exposure will result in more pulses required to reach a maximumtemperature steady state as more thermal energy must dissipate tosurrounding tissue through heat conduction.

Discussion

A. Process of Elimination Approach for Uncovering the BiophysicalMechanism:

Results presented in this example provide both theoretical andexperimental evidence that the electric field inherent in laser light isnot responsible for the low level laser excitation of neural tissue.Calculations based on experimental data predict this stimulationmechanism is unlikely. The maximum current delivered to the tissuesurface during threshold optical stimulation was 0.05 mA/mm². Thistheoretical prediction is between three and four orders of magnitudebelow the electrical stimulation threshold for peripheral nervesdetermined in the previous studies, where 0.95+/−0.58 A/cm² was requiredfor surface stimulation. Moreover, it is important to realize that theelectric field owing to light oscillates at 10¹⁴-10¹⁵ Hz, which wasagain orders of magnitude higher than the typical electrical stimulationfield oscillator frequency. To experimentally test this proposition, thevisible alexandrite laser operating at 750 nm was used to attemptoptical nerve stimulation. This wavelength, unlike the Ho:YAGwavelength, has minimal absorption in soft tissue, however, the electricfield of intensity is similar regardless of wavelength. Thus, anystimulation reported is a direct result of the electric field of thelaser light, not from absorption driven photobiological effects. Adirect electrical field is highly unlikely as a means for opticalstimulation since light from the alexandrite laser did not stimulate atradiant exposures, and therefore a maximum electric field, greater than100 times higher than those used for the Ho:YAG laser. The results fromthese experiments do support a thermally mediated mechanism. Heating ofthe tissue at damaging radiant exposures resulted in stimulation of thetissue. The carbonization and dehydration (‘burning’) of the nervesignificantly changed the optical and thermal properties of the tissue.In this case the tissue absorption for this wavelength increased andimmediately mediated the stimulatory effect. This evidence supports anabsorption driven process as the biophysical mechanism underlyingoptical stimulation.

Photochemical effects from laser irradiation depend on the absorption oflight to initiate chemical reactions. In the embodiment, it is examinedwhether the mechanism for transient optical nerve stimulation is aresult of photochemical effects from laser tissue interaction. Previousstudies have shown that stimulation threshold exhibits a wavelengthdependence based on the absorption coefficient of nerve tissue. Optimalwavelengths have a penetration depth of 300-500 microns, however, allinfrared wavelengths with sufficient tissue absorption can cause neuralstimulation. The stimulation thresholds in the infrared part of thespectrum in essence follow the water absorption curve [1] suggestingthat no “magical wavelength” has been identified. This effectivelydisproves the notion that a single tissue chromophore is responsible forany direct photochemical effects. This also provides some evidence thatthe effect is directly thermally mediated or a secondary effect tophotothermal interactions (i.e. photomechanical effects) as tissueabsorption from laser irradiation can be directly related to the heatload experienced by the tissue. Theoretically, one can predict that aphotochemical phenomenon is not responsible since infrared photon energy(<0.1 eV) is too low for a direct photochemical effect of laser tissueinteractions and insufficient for any multiphoton effects [26, 27].

Photomechanical effects produce forces, such as explosive events andlaser-induced pressure waves, which can impact cells and tissue. Sinceit is been operating well below the ablation threshold, ablative recoilcan be excluded as a source of mechanical effects. Nerve stimulationusing pressure waves (rapid mechanical displacement, ultrasound) is welldocumented in the literature [28,29]. The results section describedexperimental data that discounts the two plausible photomechanicaleffects leading to optical stimulation; thermoelastic expansion orpressure wave generation from rapid heating. As mentioned previously,relationship between laser penetration depth and pulse duration providecritical information concerning confinement of the laser energy in bothspace and time. FIG. 10 is a well known graph in tissue optics thatdepicts the relationship between these two laser parameters to definetheoretical zones separating stress confinement, thermal confinement,and no confinement of the laser pulse. The three lasers used in thecomparison between pulse duration and stimulation threshold (as shown inFIG. 2) are labeled in FIG. 10. Note that each of these lasers isthermally confined, or the pulse width is adequately short to curtailheat diffusion during the pulsed energy deposition. Similarly, the pulsewidth is satisfactorily long such that stress effects and pressure wavepropagation are minimal. If it is assumed that some level of pressuretransients are generated in tissue and these waves result in tissuestimulation, then it would be expected that the stimulation threshold todecrease (i.e. it becomes easier to stimulate using the FEL 5 μsecpulse) the closer a laser lies to the stress confinement zone. However,it is clearly to see the difference in threshold radiant exposures isnot significant over three orders of magnitude change in pulse durationwith equivalent penetration depths across the thermal confinement zone.Thermo-elastic expansion will always result from heating tissue;however, pressure waves are not generated in tissue with theseexperimental parameters for optical stimulation.

Given that there is strong evidence against laser-induced pressure wavesunderlying the optical stimulation mechanism (the pulse duration is toolong to facilitate stress confinement and indeed negligible stresstransients were measured) and given the fact that no significantdifference was found in stimulation thresholds from the three lasersources, despite a 1000 fold difference in pulse duration, it isplausible to assume that stimulation is not dependent on the pulseduration provided the pulse is short enough to minimize heat diffusionduring the laser pulse (i.e. conditions of thermal confinement arefulfilled). Although theory predicts that the pulse length may bestretched up to 100's msec before no confinement is achieved (see FIG.10), experimentally this is an overestimate. Heat diffusion beginsimmediately (see FIG. 8), which causes the quality of the evokedpotentials to be significantly diminished with laser pulse widthsgreater than 10 msec. Pulses delivered in a time less than this valueresult in crisp potentials with every pulse, however, pulses longer than10 msec tend to have a more intermittent and lethargic response. In thecase of motor axon stimulation this functionally presents as anirregular and disjointed muscle contraction as opposed to a fast,reliable twitch with shorter laser pulse durations.

While it is possible that pulsed laser irradiation induces pressurewaves in the target tissue owing to the thermoelastic effect, thecontributions of this to optical stimulation are expected to be minimalwith the laser parameters used; pulse duration of 350 μs exceeds thestress confinement time for this wavelength by nearly 3 orders ofmagnitude resulting in a dissipation of thermally induced expansionduring the laser pulse and consequently little pressure buildup [30,31].The results from DP-OCT surface displacement measurements support thisnotion and identify the exact relationship between laser radiantexposure and the subsequent upper limit in magnitude of thermoelasticexpansion in nerve tissue. Results from the successive piezoelectricactuator experiments reveal that pressure transients delivered to thenerve surface in a manner analogous to laser induced thermoelasticexpansion waves are not capable of initiating action potentials withamplitudes at least 30 times those measured for optical nervestimulation threshold. These experiments prove that temperature inducedvolumetric expansion is trivial for radiant exposures much greater thanthreshold and indicate that the mechanism lacks photomechanicalcontributions.

B. Supporting Evidence for a Photothermal Mechanism:

Through this process of elimination approach to divulge the mechanismresponsible for transient optical stimulation of nerves, it issystematically shown that electric field, photochemical andphotomechanical effects from laser tissue interactions do not result inexcitation of neural tissue. Thus, the laser stimulation of nerves ismediated by some photothermal process resulting from transientirradiation of peripheral nerves using infrared light. The spatial andtemporal thermal transients following optical stimulation of peripheralnerve for the physiologically valid range of radiant exposuresimplemented with this methodology.

Despite the fact that the process of elimination approach suggests themechanism is purely a thermal effect in the tissue driving actionpotential stimulation, proof of this concept has fundamentalsignificance. Results shown in FIG. 4 clearly show that all opticalenergy must be absorbed by the incident peripheral nerve before anystimulatory effect can occur. This implies that, in the absence ofpressure transients, the tissue must sustain some minimal thermal changebefore excitation of the underlying axons can occur. In subsequentparagraphs the nature and magnitude of the mandatory temperature changewill become apparent. These results further illustrate the importance ofpulse width in optical stimulation; predicting that longer pulses willincrease the time required for an evoked CNAP and decrease theprobability of stimulation due to onset of thermal diffusion in tissue.Further proof of the thermal nature of the biophysical mechanism lies inresults from the Alexandrite laser stimulation of the peripheral nerve.As optical and thermal properties in the tissue changed from tissuedehydration, the absorption of the alexandrite increased andsubsequently a decrease in the stimulation threshold radiant exposureswas reported. Again, these results clearly support a thermally mediatedexcitation means.

A mechanism that is thermally sustained naturally introduces query as tothe nature of the temperature change required in the tissue, which isdetermined by questioning whether this stimulatory thermal changerequires a minimum absolute value or rather a thermal gradient, a timedependent temperature change. Results discussed to this point validateeither claim, however, data collected regarding temperature dependenceon stimulation threshold help to make this distinction. Results from thethreshold dependence on nerve tissue temperature experiments demonstrateno significant change in the radiant exposure required for stimulationwith changes in tissue temperature. This is despite the fact that atissue temperature change of 25° C. in the nerve air interfaceexperimental setup requires a radiant exposure of at least 1 J/cm² (seeFIG. 7). The radiant exposures necessary for this temperature change inthe saline submerged nerve interface experimental setup (i.e. frogtemperature experiments) will require a much larger radiant exposure fora 25° C. change, at least two times the energy used for stimulation.Regardless, the stimulation thresholds are not significantly differentacross a large tissue temperature range, varying by an average of 6%between trials. From these results, it is concluded that there is no setthreshold tissue temperature that must be reached to initiate the actionpotential, as the threshold for optical stimulation does not change withlarge tissue temperature differences upon laser pulses associated onlywith small increase in tissue temperature. Thus, the mechanism foroptical stimulation is temperature dependant and a transient phenomenonrequiring a certain increase in temperature in a given short time (i.e.the laser pulse width).

The dependence of onset time for the recorded response on laser radiantexposure validates the assumption that the biophysical mechanism foroptical stimulation is rooted in temperature increases at the axonalmembrane. Internal conversion and subsequent tissue heating occurs on afemtosecond time scale, which can be considered instantaneous based onthe microsecond time scales in the discussion. Accordingly tissueheating occurs as soon as the laser light is deposited in the tissue. Asdescribed previously, the temperature increase in nerve tissue(mediating the mechanism of stimulation) is directly proportional tolaser radiant exposure, which is delivered uniformly in time by theoptical nerve stimulator. Thus, it is expected that if laser radiantexposure used to stimulate the nerve is doubled, the temperature willincrease to threshold in half the time and the onset time in therecorded response should occur in half the pulse width of the laser.This effect is clear in FIG. 5. FIG. 5 c uses double the radiantexposure used in FIG. 5 b, which is slightly above stimulation thresholdfor this particular nerve (0.5 J/cm2). At stimulation threshold theaction potential propagation occurs once all optical energy has beendeposited in tissue (as shown in FIG. 4). Conduction velocity of theaction potential is constant regardless of laser radiant exposure;consequently the propagation time from stimulus to recording is the samefor FIGS. 5 b and 5 c. With a conduction time for stimulus to recordingof about 1.8 msec, the onset of propagation in FIG. 5 b occurs at 5.8msec with a 6 msec laser pulse. Assuming the same conduction time forFIG. 5 c, however, the onset of propagation occurs at 2.8 msec. FIG. 5provides experimental proof that radiant exposures greater thanthreshold will initiate action potentials before completion of the laserpulse indicating propagation will begin as soon as the temperature riserequired for excitation (threshold temperature at the axonal membrane)is reached. Note the probability of stimulation is increased withincreasing radiant exposure and more axons are recruited leading to agreater magnitude in the response.

C. Defining the Nature and Magnitude of Thermal Gradient for OpticalStimulation:

Phototothermal effects include a large group of interaction typesresulting from the transformation of absorbed light energy to heat,leading to a local temperature increase and thus a temperature gradientboth in time and in space. It is essential to emphasize that thermalinteractions in tissue are typically governed by rate processes, whereboth the temperature and time are parameters of major importance. Heatflows in biological tissue whenever a temperature difference existsaccording to the laws of thermodynamics. The primary mechanisms of heattransfer to consider include: conduction, convection, and radiation[32]. This section details and quantifies the spatial and temporalgradients required for optical nerve stimulation.

The understanding that a thermal gradient in the target nerve is thebiophysical mechanism for excitation combined with knowledge of theextent of these temperature rises affords incite into some fundamentallimitations and optimal parameters for appropriate use of thistechnique. First, some conclusions on the spatial selectivity of thistechnique can be drawn. It is somewhat surprising that the temperatureprofile follows a Gaussian distribution in space (as shown in FIG. 6)with such a small optical fiber to tissue distance (0.5 mm), sinceVerdaasdonk and Borst (REF) have shown a more uniform beam shape at thisdistance. Thus, the spot calculated using the angle of light divergencefrom the fiber (NA=0.39, divergence=23°) assuming a uniform beam(roughly 1 mm²) is actually a larger estimation than the Gaussian spotsize calculated in the example (0.37 mm²). Assuming a specifictemperature rise is responsible for action potential generation withpulsed light, the effective stimulation area must occur within a verysmall spot where the peak temperature change within the tissue is high.It can be inferred from the temperature change versus position graphs inFIG. 6 that near stimulation threshold the effective radius is confinedto the tip of the Gaussian curve, on the order of 200 μm or less. Thisvalidates the extremely high spatial precision seen with TONS and thetechnique's ability to excite discrete populations of axons withinindividual nerve fascicles. Note the optical fiber size used in theseexperiments has a 600 μm diameter; therefore the affected tissue area isactually smaller than the size of the fiber and obviously significantlysmaller than the zone of irradiated tissue if a Gaussian beam profiledevelops. If the laser energy is increased, a greater tissue radius willovercome the required temperature change threshold. As a result, theselectivity will ultimately decrease as a greater area (thus greaternumber of axons) will be excited by the incident laser beam.Theoretically, the minimum spot size for optical stimulation is limitedonly by light diffraction and no doubt can be delivered to tissue via 10μm optical fibers.

Secondly, an upper limit to the range of non-damaging laser radiantexposures for low frequency optical stimulation is obtained. Theliterature suggests that thermal changes to mitochondria may begin tooccur with temperatures as low as 43° C. [33,34], while proteindenaturation begins at tissue temperatures close to 56-57° C. [17]. Asshown in FIG. 7, this temperature corresponds to an onset of thermalchanges in peripheral nerve connective tissues with radiant exposures aslow as 0.75 J/cm², while thermal damage to the actual underlying axonswill require laser energies greater than this value based on theexponential nature of tissue absorption. These results support thereported tissue damage threshold radiant exposures determined fromhistological analysis of short term laser nerve stimulation (0.8-1.0J/cm²) [1]. Owing to the fact that the nerve is exposed through an openincision and hydrated with room temperature saline (baselinetemperature=27° C.), the maximum temperature rise at threshold is stillbelow normal body temperature (36° C.) and therefore well belowtemperatures required for thermal changes or tissue damage. Theseresults imply that optical stimulation of peripheral nerves are mediatedthrough surface thermal gradient of 7-10° C. temperature rises.Furthermore, this phenomenon is theoretically non-damaging in peripheralnerve tissue with radiant exposures at least two times the thresholdrequired for action potential generation.

Finally, the upper limits for repetition rate without leading tosuperposition of temperature in tissue upon multiple pulses aresurmised. One can deduce from FIG. 8 that temperature superposition willbegin to occur at higher repetition rates (>4-5 Hz) as the tissuerequires slightly greater than 200 msec to return to baselinetemperature. At repetition rates greater than 5 Hz, or one pulse every200 msec, tissue temperatures will become additive with each ensuinglaser pulse and resulting tissue damage may begin to occur with longterm stimulation. This assumption is supported by the results shown inFIG. 9. With low frequency stimulation (FIG. 9 a) the resultant heatload in tissue following the laser pulse has adequate time to diffuseout of the irradiated zone via heat conduction. Alternatively, higherfrequency stimulation is clearly marked by temperature superposition asadditional pulses become additive to the overall tissue temperature.Conduction is overcome by the frequency of laser pulses and within 5 to10 pulses a steady state temperature and baseline are achieved.According to the results shown in FIG. 6 a damage will occur withchanges between 18 and 20° C. Temperature increases greater than thoserecorded in the high frequency stimulation experiment are approachingthis upper limit using threshold value radiant exposures. FIG. 9 bplainly shows that the upper limit for the frequency of opticalstimulation is 5 Hz.

Photothermal interaction leading to temperature increase is highlydependent on the optical properties of the nerve such as absorption andscattering coefficient and thermal properties such as thermalconductivity and specific heat [35]. In the infrared, the diameter ofthe sciatic nerve is much larger when compared with the penetrationdepth of the light stimulus employed. This implies that all light energythat enters the tissue is trapped inside except losses from diffusereflection. Absorption coefficients are very high compared to theeffective scattering in this wavelength range because soft tissue isdominated by forward scattering (g is about 0.9) [36]. Thereforeabsorption alone is the significant factor for interaction of the laserlight with tissue and scattering does not play a significant role in thelight distribution and resulting light induced effect on the nervoustissue. To calculate the percentage of surface temperature that reachesthe axonal layer in peripheral nerve, Beer's Law is employed and thefollowing assumptions are made: (a) absorption dominated laserpenetration (μ_(a)(λ)=3 mm⁻¹ for λ=2.12), (b) peripheral nerveconnective tissue (epineurium, perineurium, endoneurium) is a homogenoustissue, (c) the average thickness of the layers surrounding the axonallayer is 150 μm, (d) the minimum surface temperature rise required foroptical stimulation is 7-10° C., and (e) the percentage of lightattenuation is equal to the percentage of temperature attenuation in asingle layered medium. These assumptions predict that 63.8% of the lightentering the peripheral nerve surface will remain at the average depthof the axonal layer for selective stimulation of a specific fascicle.Thus, the temperature rise required at the surface of the Schwann cells(myelination) surrounding the axonal membrane to result in opticalstimulation of excitable neural tissue is approximately 4.5-6.4° C. Alltypes of neural tissues can be optically stimulated with the use ofoptimal laser parameters based on tissue structure and morphology.However, it is important to understand that some physical substance(i.e. connective tissue) to hold the thermal gradient drasticallydecreases the required radiant exposure needed to facilitate neuralexcitation. Therefore, to selectively excite cultured neurons in a largebath medium may require one of three things: 1) a greater radiantexposure that reported here, 2) an exogenous chromophore, or 3) aspecific wavelength targeting substances that lie close to the axonalmembrane to establish the necessary thermal gradient and cause thedesired stimulatory effect.

D. Possible Physiological Stimulation Mechanisms from a ThermalGradient:

It is well known in electrical stimulation that membrane depolarizationoccurs at the cathode where the concentration of negative potential, orcharge density, reduces the potential difference across the membranesubsequently activating voltage gated ion channels leading to atransmembrane current from capacitive conductance and action potentialpropagation [37]. The results presented in the example imply that atemperature rise leading to a thermal gradient is established at theaxonal membrane level upon pulsed laser irradiation and provide evidencethat this type of microscale thermal interaction is the biophysicalmechanism of optical nerve stimulation. Information on the biophysicalmechanism now helps guide experimental research in pursuit of aphysiological mechanism at the membrane level. The microscopic heatingeffects taking place at the cellular level, such as the heating ofcellular organelles or changing of channel gating kinetics are notverified through these experiments; however, some plausible explanationsfor this photobiological phenomenon are given.

Temperature can affect action potential propagation in three ways: 1)the Nernst equilibrium potentials are inversely proportional to theabsolute temperature, 2) the probability of ion channel opening istemperature dependent, and 3) a change in temperature changes theamplitude and duration of the signal by a common temperature factorgoverning the rate for channel induction called a Q10 [38]. Onepotential hypothesis for the physiological mechanism for opticalstimulation is the activation of heat sensitive channels, where thegating mechanism is markedly different from the other channel types;voltage gated, ligand gated, and mechanosensitive ion channels. Theequilibrium change from closed to open states for all channel typesdepends on the temperature dependent Gibbs free energy change. A reviewof the known ion channels gated by heat is given by Cesare, et al [39]who suggests that this temperature rise causes the heat sensitivechannels to change to a more disordered state. No accessory proteins orsignaling pathway is responsible for the gating of these channels,rather some intrinsic gating unit within the channel [40,41]. Thesechannels can undergo sensitization which causes a shift in therelationship linking temperature to the probability that a channel isopen toward a lower temperature [42]. This may explain the reason atemperature rise and not an absolute temperature is required foractivation. The known heat sensitive channels responding to increase intemperature all have extremely large Q(10) values (>10) and include; theTREK-1 potassium channel and 5 cation channels from the transientreceptor potential family, vianilloid subfamily [43,44]. TRPV1, 2, and 3are highly expressed in the dorsal root ganglia. Of these, the TRPV1 andTRPV3, Specifically, TRPV1 and TRPV3 are the likely candidates fortargeted optical stimulation because they open at about 38 degrees C. Itis well known that these channels are expressed afferent sensory neurons[45], however recent evidence supports the existence of TRPV1 inefferent fibers [46]. A second hypothesis involves Na channel activationbased on a local increase in the probability of channel transition toopen resulting from a temperature increase. It is assumed that this is alikely candidate since sodium channels typically initiate the onset andpropagation of a potential in a stimulated axon. The Q10 values forthese channels are significantly lower than those of the heat sensitivechannels, however, with the abundance of sodium channels in the axontogether with the temperature increases implicated in this paper fromoptical stimulation the initiation of a localized sodium currentsufficient for stimulation is certainly plausible.

In sum, the results presented in the example reveal that neuralactivation with pulsed light occurs by a transient thermally mediatedmechanism. The electric field effect, photochemical means, andphotomechanical mechanisms are discarded as possible means foractivation of nerve potentials. Data collected reveal that the spatialand temporal nature of this temperature rise, including a measuredsurface temperature change required for stimulation of the peripheralnerve (7-10° C.) and at the axon level (4.5-6.4° C.). This informationhas been used to detail the limits in selectivity, pulse duration, andrepetition rate using this technique in the peripheral nerve.Ultimately, it is envisioned that this information will form the basisfor the development of a portable, hand-held device for opticalstimulation based on solid state diode laser technology, operating atthe optimal laser parameters to incite a safe and effective motorresponse. Such a device would have utility in both basicelectrophysiology studies as well as clinical procedures that currentlyrely on electrical stimulation of neural tissue.

The foregoing description of the exemplary embodiments of the inventionhas been presented only for the purposes of illustration and descriptionand is not intended to be exhaustive or to limit the invention to theprecise forms disclosed. Many modifications and variations are possiblein light of the above teaching.

The embodiments were chosen and described in order to explain theprinciples of the invention and their practical application so as toenable others skilled in the art to utilize the invention and variousembodiments and with various modifications as are suited to theparticular use contemplated. Alternative embodiments will becomeapparent to those skilled in the art to which the present inventionpertains without departing from its spirit and scope. Accordingly, thescope of the present invention is defined by the appended claims ratherthan the foregoing description and the exemplary embodiments describedtherein.

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What is claimed is:
 1. An apparatus for stimulating a neural tissue of aliving subject, wherein the neural tissue is characterized with athermal diffusion time, T_(d), comprising: a. an energy source forgenerating optical energy; and b. a delivering means coupled to theenergy source for delivering the generated optical energy to a targetneural tissue, wherein the delivering means is configured to inoperation deliver the generated optical energy with a radiant exposurethat causes a thermal gradient in the target neural tissue, therebystimulating the target neural tissue, and to deliver the optical energyin pulses with a pulse duration T_(p) such that T_(p)<T_(d).
 2. Theapparatus of claim 1, wherein the delivering means comprises: a. aconnector having a body portion defining a channel extending from afirst end to a second end; b. one or more optical fibers housed in thechannel for transmitting the optical energy; and c. a probe operablycoupled to the second end of the connector and having an end portion fordelivering the optical energy to a target neural tissue.
 3. Theapparatus of claim 2, wherein the delivering means further comprises aselecting device operably coupled to the connector for selectivelydelivering the optical energy through at least one of the one or moreoptical fibers.
 4. The apparatus of claim 3, wherein the deliveringmeans further comprises a movable stage that is operably coupled to theprobe such that the probe is movable with the movable stagethree-dimensionally to selectively deliver the optical energy to one ormore neural fibers of the target neural tissue.
 5. The apparatus ofclaim 1, wherein the delivering means comprises: a. a first opticalmeans for directing the optical energy to a desired direction; and b. asecond optical means for focusing the optical energy directed by thefirst optical means to a target neural tissue, wherein the first opticalmeans and the second optical means are positioned such that the energysource, the delivering means and the target neural tissue are positionedalong an optical path.
 6. The apparatus of claim 5, wherein each of thefirst optical means and the second optical means comprises at least oneof one or more optical mirrors, one or more optical lenses, one or moreoptical couplers, and one or more optical fibers.
 7. The apparatus ofclaim 1, further comprising a controlling means operably coupled to theenergy source and the delivering means and the target neural tissue, thecontrolling means comprising: a. a first detector operably coupled tothe energy source for measuring the optical energy generated from theenergy source; b. a second detector operably coupled to the targetneural tissue for measuring the thermal gradient in the target neuraltissue; and c. a computer operably coupled to the first detector and thesecond detector for evaluating the optical stimulation of the targetneural tissue.
 8. The apparatus of claim 1, wherein the energy sourcecomprises a laser capable of generating a beam of optical energy havinga wavelength that is fixed or tunable.
 9. The apparatus of claim 8,wherein the laser comprises a pulsed infrared laser.
 10. The apparatusof claim 8, wherein the laser comprises a free electron laser, anAlexandrite laser, a solid state laser, a CO₂ laser, a tunable opticalparametric oscillator (OPO) laser system, an N₂ laser, an excimer laser,a Holmium-doped:Yttrium Aluminum Garnet (Ho:YAG) laser, or an Erbiumdoped: Yttrium Aluminum Garnet (Er:YAG) laser.